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EP0122035A1 - Medizinische Vorrichtung zur prophylaktischen Behandlung von Decubitus Ulcer - Google Patents

Medizinische Vorrichtung zur prophylaktischen Behandlung von Decubitus Ulcer Download PDF

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Publication number
EP0122035A1
EP0122035A1 EP84301543A EP84301543A EP0122035A1 EP 0122035 A1 EP0122035 A1 EP 0122035A1 EP 84301543 A EP84301543 A EP 84301543A EP 84301543 A EP84301543 A EP 84301543A EP 0122035 A1 EP0122035 A1 EP 0122035A1
Authority
EP
European Patent Office
Prior art keywords
gel
film
envelope
hydrophilic
mobile
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Granted
Application number
EP84301543A
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English (en)
French (fr)
Other versions
EP0122035B1 (de
Inventor
Ian Alexander Buchan
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Smith and Nephew PLC
Original Assignee
Smith and Nephew Associated Companies PLC
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from GB838306663A external-priority patent/GB8306663D0/en
Priority claimed from GB838329877A external-priority patent/GB8329877D0/en
Application filed by Smith and Nephew Associated Companies PLC filed Critical Smith and Nephew Associated Companies PLC
Priority to AT84301543T priority Critical patent/ATE27905T1/de
Publication of EP0122035A1 publication Critical patent/EP0122035A1/de
Application granted granted Critical
Publication of EP0122035B1 publication Critical patent/EP0122035B1/de
Expired legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/42—Use of materials characterised by their function or physical properties
    • A61L15/60—Liquid-swellable gel-forming materials, e.g. super-absorbents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F13/00—Bandages or dressings; Absorbent pads
    • A61F13/02—Adhesive bandages or dressings
    • A61F13/023—Adhesive bandages or dressings wound covering film layers without a fluid retention layer
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61G—TRANSPORT, PERSONAL CONVEYANCES, OR ACCOMMODATION SPECIALLY ADAPTED FOR PATIENTS OR DISABLED PERSONS; OPERATING TABLES OR CHAIRS; CHAIRS FOR DENTISTRY; FUNERAL DEVICES
    • A61G7/00—Beds specially adapted for nursing; Devices for lifting patients or disabled persons
    • A61G7/05—Parts, details or accessories of beds
    • A61G7/057—Arrangements for preventing bed-sores or for supporting patients with burns, e.g. mattresses specially adapted therefor
    • A61G7/05738—Arrangements for preventing bed-sores or for supporting patients with burns, e.g. mattresses specially adapted therefor with fluid-like particles, e.g. sand, mud, seeds, gel, beads
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/22—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons containing macromolecular materials
    • A61L15/26—Macromolecular compounds obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds; Derivatives thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L15/00—Chemical aspects of, or use of materials for, bandages, dressings or absorbent pads
    • A61L15/16—Bandages, dressings or absorbent pads for physiological fluids such as urine or blood, e.g. sanitary towels, tampons
    • A61L15/42—Use of materials characterised by their function or physical properties

Definitions

  • the present invention relates to devices for application to the pressure bearing surfaces of humans, for example bedridden patients, for the prophylaxis of pressure sores.
  • devices which are particularly suitable for application to those areas of the patient such as the heel and sacrum which are most at risk of developing pressure sores which device comprises a hydrophilic mobile gel retained within a flexible, elastomeric envelope.
  • methods of forming such devices and to their use as pads which maybe applied to the body of the patient for the prophylaxis of pressure sores.
  • a prophylactic device.consisting of a cross-linked water insoluble immobile polyurethane gel contained within an outer envelope has been described in European Patent Specification No. 0,057,838.
  • the prophylactic device described in European Patent Specification No. 0,057,838 is adapted to be used as a cushion or a mattress and as such- is only providing protection to the patient when the patient is actually in position on the prophylactic device. If the patient is moved from his bed or chair, where he is on the prophylactic device for example to another bed, a chair, then he will no longer be afforded protection. Also it is found that a mobile gel filled device is more effective than the cross-linked immobile gel filled device at reducing the pressures experienced by a patient when lying on one of these devices and has greater conformability.
  • the present invention provides a device suitable for the prophylaxis of pressure sores which device comprise a gel retained within a flexible elastomeric envelope which envelope has a body contacting surface which is a film having a moisture vapour transmission rate of greater than 300g/m 2 /24hr- 1 at 37 0 C at 100% - 10% relative humidity difference characterised in that the device is 5.0 to 25mm thick and may be worn on the body and the gel is a mobile moisture absorbing hydrophilic gel.
  • Suitable examples for the film which contacts the body of the wearer of the device are backing materials described in British Patent Specification No. 1280631 which is incorporated herein by cross reference.
  • Apt polymers for forming the film are polyurethanes such as those known as Estane (Registered Trade Mark). Suitable Estanes include Estane 5702, 5701, 5714F and 58201. Other preferred polymers for forming the film are polyetherester block copolymers such as Hytrel (Registered Trade Mark). Suitable Hytrels include Hytrel 4056. Yet other preferred polymers for forming the film are polyether polyamide copolymers such as Pebax (Registered Trade Mark). Suitable Pebax include Pebax 2533 SN 00.
  • the thickness of the film employed in the device of this invention is chosen to produce the desired moisture vapour transmission rater (MVTR).
  • MVTR moisture vapour transmission rater
  • the thickness of the film which will give the correct MVTR and be sufficiently strong to withstand the pressure applied to it will be in the range 25 to 100 microns.
  • the film will be chosen so that its MVTR will be greater than 300g/m 2 /24hr- 1 and preferably will be greater than 500g/m 2 24hr -1 , at 37°C and at 100% - 10% relative humidity.
  • the hydrophilic gel may be retained between a film which is to contact the skin of the wearer which has the MVTR set out in the preceeding paragraph and a film having a lower MVTR (for example one which for practical purposes is a moisture vapour impermeable film).
  • the moisture vapour impermeable film may be a polyolefin, polyvinylchloride or the like.
  • the surface of the device which is to-contact the skin may carry an adhesive layer whereby the device may be adhered to the skin in use.
  • an adhesive layer whereby the device may be adhered to the skin in use.
  • Suitable adhesives must be compatible with the skin, thus they will normally be hypoallergenic.
  • the adhesives will be synthetic polymers or mixtures thereof. Such adhesives may be selected from those described in British Patent Specification No. 1280631 and European Patent Application No. 35399, both of which are incorporated herein by cross-reference.
  • Preferred adhesives are those which have an MVTR such that the adhesive together with the film which is in contact with the skin has an MVTR of greater than 300gm -2 24hr- 1 and more preferably greater than 500gm -2 24hr -1 when measured at 37 0 C and 100% - 10% relative humidity.
  • Suitable adhesives include those formed from polyacrylates or polyvinyl ethers.
  • the adhesive will be applied to the film in the form of a continuous layer. However it is envisaged that the adhesive could be applied to form a discontinuous layer such as a pattern spread layer. If desired the adhesive may incorporate an antibacterial agent such as a chlorhexidine salt.
  • the film which forms the envelope may be extended to form a margin or flange around the gel- filled envelope.
  • the body contacting layer will preferably carry an adhesive layer for adhering the device to the skin. This layer may be present over the whole of the device's surface or only on the margin.
  • the adhesive layer may be a continuous layer or a discontinuous layer such as a pattern spread layer.
  • the non-body contacting film may extend beyond the envelope and be coated on the side which may be brought into contact with the body with a suitable adhesive.
  • the surface of the device which is to contact the skin may carry an adhesive layer whereby the device may be adhered to the skin in use.
  • the device can remain in position for a week or even longer. During this period the moisture produced by normal perspiration of the skin under the device must be removed otherwise the skin will become waterlogged and degenerate. It has now been found that this can be achieved if the moisture is transmitted through the wall of the envelope and absorbed by the gel.
  • the gel in the envelope is therefore selected to be hydrophilic and absorb the moisture generated by the skin during the wearing period.
  • the gel is suitably introduced into the envelope in an anhydrous state so that the gel is chosen to be jelly-like and mobile even when anhydrous.
  • Suitable hydrophilic mobile gels include polyurethanes, polyethylene glycols, and polyoxyethylene-polyoxypropylene diol block copolymer gels which have the correct viscosity characteristics and are capable of flowing in a manner which distributes an applied pressure approximately evenly over their surface.
  • Apt mobile hydrophilic gels are hydrophilic polyurethanes described in, for example International Application No. WO 82/01306, which is incorporated herein by cross-reference.
  • Preferred hydrophilic mobile gels are linear polyether polyurethanes formed from random polyoxyethylene-polyoxypropylene diol copolymers and a di-isocyanate.
  • Preferred random polyoxyethylene-polyoxypropylene diol copolymers include Breox 75W-270 (Registered trade mark).
  • the preferred linear polyether polyurethanes are made by mixing the appropriate volume of random polyoxyethylene-polyoxypropylene diol copolymer, di-isocyanate such as Desmodur W (Registered Trade Mark) and an antioxidant such as Irganox 1010 (Registered Trade Mark) together and heating to a temperature of between 40°C and 90 0 C and preferably between 60°C and 70°C and then adding a catalyst such as dibutyl tin dilaurate. The mixture is then maintained at a temperature between 70°C and 110°C and preferably between 80°C and 100°C until the reaction is complete.
  • di-isocyanate such as Desmodur W (Registered Trade Mark) and an antioxidant such as Irganox 1010 (Registered Trade Mark)
  • a catalyst such as dibutyl tin dilaurate
  • the preferred linear polyether polyurethanes are made from random polyoxyethylene-polyoxypropylene diol copolymers and a di-isocyanate with a ratio of isocyanate groups (NCO) to hydroxyl groups (OH) of between 0.3 to 0.9 and more preferably 0.5 to 0.7. Such preferred polyurethanes will absorb at least 10% water.
  • the visosity (as measured at 39°C using a Ferranti-Shirley Cone and Plate Viscometer with a lcm radius cone and a 1200g spring) of the preferred linear polyether polyurethane will suitably be between 500 and 10,000 Poise and preferably be between 1,500 and 6,000 Poise, for example 3,000 Poise.
  • hydrophilic mobile gel and film forming the walls of the envelope and the adhesive when present are suitably transparent so that the condition of the skin beneath the device may be monitored during the wearing period.
  • the hydrophilic mobile gel may incorporate a substance, for example a cobalt salt, which will indicate by virtue of a colour change when the percentage of water absorbed into the gel has reached a certain level e.g. 50% indicating that the device should be replaced.
  • a substance for example a cobalt salt
  • the hydrophilic mobile gel may incorporate less dense materials, for example glass or polystyrene microspheres so that a prophylactic device, when made from the hydrophilic mobile gel incorporating these less dense materials, will be lighter than an equivalent device made from the hydrophilic mobile gel alone.
  • the envelope may be formed by conventional means from the appropriate polymer film.
  • the film may be formed into strips of the appropriate size, folded and heat sealed along two sides to provide an envelope with an opening or the envelopes may be blow moulded or vacuum formed from suitable polymer.
  • the size and shape of the device will vary depending upon the area of the body to which the device is to be applied.
  • pressure bearing surface is meant those surfaces upon which the weight of a patient rests when, for example, in a prone position where the pressure bearing surfaces are for example the heels, sacrum and shoulder blades.
  • Certain apt devices of the invention contain at least two compartments.
  • the first compartment is adapted to be placed beneath the pressure bearing surfaces of a prone or sitting patient.
  • Such compartments are generally rectangular or square.
  • the other compartments are present to give support to the body adjacent to the pressure bearing surfaces. With the heel this surface is the arch between the heel and-the calf; with the sacrum it is the arch of the back.
  • These compartments may be filled with gel so that they may be firmer than those supporting a pressure bearing surface.-
  • These compartments are shaped to take account of the contours. These compartments may provide support rather than disperse pressure but they should not be so firm as to create new pressure sores.
  • the envelope comprises two sealed compartments.
  • the compartments are not in fluid communication with each other so that when the heel or sacrum is placed on the appropriate compartment the pressure is dissipated over that compartment only.
  • the heel or sacrum pressure bearing compartments will vary in size depending upon the area with which they are in contact but aptly in shape they will be in the form of a rectangle including a square.
  • the pressure bearing compartment will suitably be in the form of a square the side of which is from 40 to 75mm and preferably 55 to 60mm long and is from 5 to 25mm and preferably 10 to 15mm in thickness and containing from 8 to 50ml, preferably 20 to 30ml of hydrophilic gel material.
  • the pressure bearing compartment will be suitably in the form of a rectangle which has a short side of from 40 to 60mm in length, preferably 45 to 55mm and a long side of from 80 to 120mm, preferably 90 to 105mm in length and from 5 to 25mm and preferably 10 to 15mm in thickness.
  • Such compartments will contain from 20 to 150ml of hydrophilic gel and preferably 25 to 50ml of hydrophilic gel.
  • the second sealed compartment is shaped to provide support to the non pressure bearing surfaces adjacent to the heel or sacrum. Adjacent to the heel the shape of the compartment is such that it extends along the back of the leg to the calf.
  • the shape of this compartment is that of a triangle which tapers from the heel along the leg and is also thicker adjacent to the heel and reduces in thickness along the leg.
  • the triangular compartment is suitably 40 to 75mm across its base and has a height of from 150 to 200mm from base to the tip.
  • the thickness of the compartment is suitably 18 to 25mm adjacent to the heel and 5 to 15mm thick at the pointed end.
  • This compartment will contain more hydrophilic gel than the first compartment and will suitably contain 50 to 200ml.
  • the second sealed compartment will extend to provide support for the back adjacent to the sacrum.
  • the most suitable shape is that of a trapezium in which the narrower side is adjacent to the sacrum and the sides diverge.
  • the compartment has a width of 80 to 120mm which widens to 200 to 250mm at the other edge.
  • the length of the compartment is from 120 to 150mm.
  • Aptly when not stressed this compartment is flat and is from 10 to 20mm thick.
  • the second compartment will contain from 300 to 400ml.
  • Figure 1 shows a two-compartment device (1) which is suitable for use on the heel of a bedridden patient.
  • the first compartment (2) is approximately square in shape and is filled with a mobile hydrophilic polyurethane gel to a thickness of about 10mm, the dimension of the compartment being approximately 55mm square. At this thickness the compartment provides a suitable pad for the heel.
  • the second compartment (3) is triangular in shape tapering to approximately a point away from the heel. This compartment lies along the leg from the heel to the calf.
  • This compartment is filled with a mobile hydrophilic polyurethane gel so that it is firmer to the touch than the first compartment.
  • the thickness of this compartment is 20mm narrowing to 12mm at the pointed end.
  • the walls of both compartments are formed from a moisture vapour permeable polyether polyamide block copolymer which is approximately 75 microns thick and is heat sealed around its edges to form the compartments.
  • the two compartments are not in communication being separated by a seal line (4).
  • Figure 2 shows a side view of the device shown in Figure 1. This shows the difference in thickness of the two compartments.
  • the secnd compartment (3) also has a variable thickness from the portion adjacent to the heel compartment to the point of the triangle. The thicker portion being adjacent to the heel so that the device follows the contours of the back of the leg.
  • the envelope for this compartment is conveniently formed in this three dimensional form by vacuum moulding.
  • Figure 3 shows a two compartment device (11) which is suitable for use on the sacrum of a bedridden patient.
  • the first compartment (12) is rectangular in shape and is filed with a hydrophilic polyurethane gel to a thickness of 10mm.
  • the dimensions for the compartment are typically 100mm by 55mm. At this thickness the compartment provides a suitable pad for placing beneath the sacrum.
  • the second compartment (13) is trapezoidal in shape with the narrower side of the trapezium adjaent to the sacrum bearing compartment.
  • the compartment is filled with a hydrophilic polyurethane gel so that it may be firmer to the touch than is the first compartment.
  • the thickness of this compartment is l5mm.
  • the walls of both containers are a moisture vapopur permeable polyether polyamide block copolymer which is approximately 75 microns thick and is heat sealed around the edge.
  • the two compartments are not in communication being separated by a seal line (14).
  • Figure 4 shows a side view of the device shown in Figure 3. The difference in thickness of the two compartments is clearly shown. In use on the sacrum and back the variation in thickness of the second compartment is not as critical as with the device for the heel.
  • Figure 5 shows a two compartment device (21) which is suitable for use on the heel which is similar to the device of Figure 1 except that a film carrying an adhesive is present as an adhesive margin (22) whereby the device may be adhered to the leg.
  • a film carrying an adhesive is present as an adhesive margin (22) whereby the device may be adhered to the leg.
  • both the film and adhesive are moisture vapour permeable so that the device may be left on the skin for a long period without causing maceration to the underlying skin.
  • a preferred embodiment of the present invention is a device in which one of the envelopes of the device narrows from an end to the opposed end so that one end of the envelope is wider than the other end.
  • a linear polyurethane gel was prepared from the following:
  • the first three ingredients were mixed together to form a homogenous mixture whilst warming to 60°C.
  • the catalyst was then added.
  • the di-isocyanate was added with stirring.
  • the resultant homogenous reaction mixture was poured into a mould and cured in an oven at 90°C for 2 hours.
  • the resultant hydrophilic polyurethane was obtained as a viscous, transparent, mobile gel.
  • a polyurethane film was cast onto a silicone release paper at a weight of 60gsm using a polyurethane syrup comprising 100 parts of Estane 5714F (available from B.F. Goodrich Ltd), 5 parts of Gasil 23 fine silica (available from Crossfield Chemical Ltd), 240 parts of tetrahydrofuran and 160 parts acetone.
  • the resultant film was cut into strips so that on folding each strip in half and heat sealing the two edges, an envelope approximately 10cm by 10cm was formed.
  • a part of the anhydrous polyurethane gel prepared above (120ml) was transferred to the polyurethane envelope and the envelope closed by heat sealing along the fourth edge.
  • the resultant pad 10cm by 10cm and 1.2cm thick was suitable for use to prevent formation of pressure sores on the sacrum.
  • a linear polyurethane gel was prepared from the following:
  • the first four ingredients were mixed together to form a homogenous mixture whilst warming to 60 o C.
  • the catalyst was then added with stirring.
  • the resultant homogenous reaction mixture was poured into a mould and cured in an oven at 90°C for 2 hours.
  • the resultant hydrophilic polyurethane was obtained as a viscous, transparent mobile gel.
  • a polyether polyamide copolymer film was extruded in a conventional manner using a melt temperature of approximately 185°C.
  • the resultant film thickness was approximately 170 microns.
  • This film was moulded into the appropriate shape of approximately 10cm x 10cm x 3cm deep using a vacuum mould.
  • the average thickness of the film after vacuum moulding was approximately 75 microns.
  • a part of the anhydrous linear polyurethane gel prepared above (120mls) was transferred to the pouch of polyether polyamide copolymer film formed in the vacuum mould.
  • a further piece of extruded polyether polyamide copolymer film with a thickness of 75 microns was then heat sealed to the hydrophilic gel filled pouch in such a manner as to exclude all the air from the envelope thus formed.
  • the polyether polyamide copolymer film thus sealed to the hydrophilic gel filled pouch extended on all sides by 10cm beyond the hydrophilic gel filled envelope.
  • This extended area of polyether polyamide film was coated with suitable pressure sensitive adhesive at a mass weight of 30gsm. The adhesive face of the device was then placed onto a silicone release paper and the whole device sealed into a substantially vapour impermeable bag for storage.
  • a linear polyurethane gel was prepared from the following:
  • the first four ingredients were mixed together to form a homogenous mixture whilst warming to 60°C.
  • the catalyst was then added with stirring.
  • the resultant homogenous reaction mixture was poured into a mould and cured in an oven at 90°C for 2 hours.
  • the resultant hydrophilic polyurethane was obtained as a viscous, transparent mobile gel.
  • a polyetherester block copolymer film was extruded in the conventional manner using a melt temperature of approximately 185 0.
  • the resultant film thickness was approximately 170 microns.
  • This film was moulded into the appropriate shape of approximately 10cm x 10cm x 3cm deep using a vacuum mould.
  • the average thickness of the film after vacuum moulding was approximately 75 microns.
  • a part of the anhydrous linear polyurethane gel prepared above (120mls) was transferred to the pouch of polyetherester block copolymer film formed in the vacuum mould.
  • a further piece of extruded polyetherester block copolymer film with a thickness of 75 microns was then heat sealed to the hydrophilic gel filled pouch in such a manner as to exclude all the air from the envelope thus formed.
  • the polyetherester block copolymer film thus sealed to the hydrophilic gel filled pouch extended on all sides 10cm beyond the hydrophilic gel filled envelope.
  • This extended area of polyetherester block copolymer film was coated with a suitable pressure sensitive adhesive at a mass weight of 30gsm. The adhesive face of the device was then placed onto a silicone release paper andw-the whole device sealed into a substantially water vapour impermeable bag for storage.
  • a linear polyurethane gel was prepared in the same manner as Example 2.
  • a polyether polyamide copolymer film was extruded in the conventional manner using a melt temperature of approximately 185°C.
  • the resultant film thickness was approximately 170 microns.
  • This film was moulded into the appropriate shape using a vacuum mould.
  • the appropriate shape for a device for the heel is that shown and described in Figures 1 and 2 of this specification.
  • the average thickness of the film after vacuum moulding was approximately 75 microns.
  • a part of the anhydrous linear polyurethane gel prepared above (100ml) was transferred to the larger of the two pouches of the polyether polyamide copolymer film and 25ml of the anhydrous linear polyurethane gel prepared above was transferred to the smaller of the two pouches of the polyether polyamide copolymer film formed in the vacuum mould.
  • a further piece of extruded polyether polyamide copolymer film with a thickness of 75 microns was then heat sealed to the hydrophilic gel filled pouches in such a manner as to exclude all the air from the two independent envelopes thus formed.
  • the polyether polyamide copolymer film thus sealed to the hydrophilic gel filled pouches extended on all sides bylOcm beyond the hydrophilic gel filled envelopes.
  • This extended area of polyether polyamide film was coated with a suitable pressure sensitive adhesive at a mass weight of 30gsm.
  • the adhesive face of the device was then placed onto a silicone release paper and the whole device sealed into a substantially water vapour impermeable bag for storage.
  • a linear polyurethane gel was prepared as in Example 3.
  • a polyetherester block copolymer film was extruded in the conventional manner using a melt temperature of approximately 185°C. The resultant film thickness was approximately 170 microns. This film was then moulded into the appropriate shape using a vacuum mould. The appropriate shape for a device for the heel is that shown and described in Figures 1 and 2 of this specification. The average thickness of the film after vacuum moulding was approximately 75 microns.
  • a part of the anhydrous linear polyurethane gel prepared above (100ml) was transferred to the larger of the two pouches of the polyetherester block copolymer film and 25ml of the anhydrous linear polyurethane gel prepared above was transferred to the smaller of the two pouches of the polyetherester block copolymer film formed in the vacuum mould.
  • a further piece of extruded polyetherester block copolymer film with a thickness of 75 microns was then heat sealed to the hydrophilic gel filled pouches in such a manner as to exclude all the air from the two independent envelopes thus formed.
  • the polyetherester block copolymer film thus sealed to the hydrophilic gel filled pouches extended on all sides by 10cm beyond the hydrophilic gel filled envelopes.
  • This extended area of polyetherester block copolymer film was coated with a suitable pressure sensitive adhesive at a mass weight of 30gsm.
  • the adhesive face of the devices was then placed onto a silicone release paper and the whole device sealed into a substantially water vapour impermeable bag for storage.

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  • Life Sciences & Earth Sciences (AREA)
  • Veterinary Medicine (AREA)
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  • Chemical & Material Sciences (AREA)
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  • Materials For Medical Uses (AREA)
EP84301543A 1983-03-10 1984-03-08 Medizinische Vorrichtung zur prophylaktischen Behandlung von Decubitus Ulcer Expired EP0122035B1 (de)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AT84301543T ATE27905T1 (de) 1983-03-10 1984-03-08 Medizinische vorrichtung zur prophylaktischen behandlung von decubitus ulcer.

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
GB8306663 1983-03-10
GB838306663A GB8306663D0 (en) 1983-03-10 1983-03-10 Medical device
GB838329877A GB8329877D0 (en) 1983-11-09 1983-11-09 Shaped medical device
GB8329877 1983-11-09

Publications (2)

Publication Number Publication Date
EP0122035A1 true EP0122035A1 (de) 1984-10-17
EP0122035B1 EP0122035B1 (de) 1987-06-24

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Family Applications (1)

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EP84301543A Expired EP0122035B1 (de) 1983-03-10 1984-03-08 Medizinische Vorrichtung zur prophylaktischen Behandlung von Decubitus Ulcer

Country Status (5)

Country Link
US (1) US4516571A (de)
EP (1) EP0122035B1 (de)
AU (1) AU561363B2 (de)
CA (1) CA1213487A (de)
DE (1) DE3464327D1 (de)

Cited By (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP0182462A2 (de) * 1984-09-05 1986-05-28 SMITH & NEPHEW plc Druckentlastende medizinische Vorrichtung zur Verhütung von Wundliegen
FR2651999A1 (fr) * 1989-04-28 1991-03-22 Archeny Jean Pierre Coussins et matelas anti-escarres a usage medical.
WO1991017684A1 (en) * 1990-05-23 1991-11-28 Bay Jacobsen Af 1991 A/S Cushion made from plastic foam
EP0536875A1 (de) * 1991-08-07 1993-04-14 Paul Hartmann Aktiengesellschaft Hydrogelverband
WO1996028056A1 (en) * 1995-03-15 1996-09-19 Gel Sciences, Inc. Conformable structures
US6861067B2 (en) 1998-09-17 2005-03-01 Sherwood Services Ag Hydrogel wound dressing and the method of making and using the same

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US4738257A (en) * 1986-06-11 1988-04-19 Hollister Incorporated Occlusive wound care dressing
US4713069A (en) * 1986-10-31 1987-12-15 Kimberly-Clark Corporation Baffle having zoned water vapor permeability
US5497789A (en) * 1987-07-20 1996-03-12 Zook; Gerald P. Foot protector incorporating a viscoelastic gel
US4979946A (en) * 1987-12-14 1990-12-25 The Kendall Company Environmental absorbent dressing
US5394890A (en) * 1991-07-10 1995-03-07 Lambert; William S. Ingrown toenail relief saddle
DE4293451T1 (de) * 1991-09-13 1994-09-08 Gillette Canada Polymerpartikel für zahnmedizinische Anwendungen
NZ248977A (en) * 1992-11-09 1995-06-27 Squibb & Sons Inc Pressure-sensitive adhesive comprising a polyurethane having excess hydroxyl functionality; medical articles comprising a layer of such adhesive
US6494418B1 (en) * 1996-02-06 2002-12-17 3M Innovative Properties Company Wrist rest assembly
US6342061B1 (en) 1996-09-13 2002-01-29 Barry J. Kauker Surgical tool with integrated channel for irrigation
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GB201006323D0 (en) * 2010-04-15 2010-06-02 Systagenix Wound Man Ip Co Bv Leakage-reducing dressing
EP2765967B1 (de) 2011-10-12 2017-03-22 Roar Consultants Wundverband-kleidungsstück
US10966471B1 (en) * 2020-05-19 2021-04-06 Aslan Medical Equipment, Llc Soft silicon edged cushion for face masks
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GB1280631A (en) * 1968-07-09 1972-07-05 Smith & Nephew Adhesive materials
EP0057838A1 (de) * 1981-02-03 1982-08-18 Bayer Ag Gel-Polster, Verfahren zu deren Herstellung und deren Verwendung
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EP0182462A2 (de) * 1984-09-05 1986-05-28 SMITH & NEPHEW plc Druckentlastende medizinische Vorrichtung zur Verhütung von Wundliegen
EP0182462A3 (en) * 1984-09-05 1987-07-08 Smith And Nephew Associated Companies P.L.C. Pressure relieving medical device suitable for the prophylaxis of pressure sores
FR2651999A1 (fr) * 1989-04-28 1991-03-22 Archeny Jean Pierre Coussins et matelas anti-escarres a usage medical.
WO1991017684A1 (en) * 1990-05-23 1991-11-28 Bay Jacobsen Af 1991 A/S Cushion made from plastic foam
EP0536875A1 (de) * 1991-08-07 1993-04-14 Paul Hartmann Aktiengesellschaft Hydrogelverband
WO1996028056A1 (en) * 1995-03-15 1996-09-19 Gel Sciences, Inc. Conformable structures
US6861067B2 (en) 1998-09-17 2005-03-01 Sherwood Services Ag Hydrogel wound dressing and the method of making and using the same

Also Published As

Publication number Publication date
AU2547984A (en) 1984-09-13
EP0122035B1 (de) 1987-06-24
AU561363B2 (en) 1987-05-07
DE3464327D1 (en) 1987-07-30
US4516571A (en) 1985-05-14
CA1213487A (en) 1986-11-04

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